Ultrasound systems and methods for optimizing multiple imaging parameters using a single user interface control

ABSTRACT

The present embodiments relate generally to ultrasound imaging systems and methods that provide a user interface on the touchscreen display. The user interface includes an ultrasound image feed and a single control for modifying imaging depth of the ultrasound image feed. When input via the single control is received to modify the imaging depth, the system: adjusts frequency of ultrasound signals being used to acquire the ultrasound image feed; adjusts a beamformer parameter of the ultrasound signals being used to acquire the ultrasound image feed; receives first image data of the ultrasound image feed based on the adjusted frequency and the adjusted beamformer parameter; based on the first image data, adjusts Time Gain Compensation (TGC) of the ultrasound image feed; and receives second image data of the ultrasound image feed based on the adjusted frequency, beamformer parameter and TGC. Display of the second image data on the touchscreen display is then optimized without receipt of additional user input.

FIELD

The present disclosure relates generally to ultrasound imaging, and inparticular, user interface controls for modifying imaging parameters onultrasound systems.

BACKGROUND

Ultrasound imaging systems are a powerful tool for performing real-time,non-invasive imaging procedures in a wide range of medical applications.An ultrasound machine includes a transducer which sends out ultrasoundsignals into tissue. Ultrasound waves are reflected back from the tissueand are received by the transducer. The reflected signals are processedto produce an ultrasound image of the target anatomy. An ultrasoundmachine typically has a user input device by which the operator of theultrasound machine can control the machine to obtain images of tissuestructures. Traditionally, the images may be displayed on a displayincorporated in the ultrasound machine, and the user input device mayinclude a keyboard.

A challenging part of acquiring ultrasound images is adjusting thevarious imaging parameters to optimize the image viewable. Conventionalultrasound systems have large physical control interfaces with numerouscontrols that allow modifying of various imaging parameters affectingthe displayed image quality. It is typically required that multiplecontrols need to be manipulated to achieve an image with good quality.The manipulation of multiple controls to optimize image quality may notbe intuitive, and users may require extensive training to learn the howthe operation of these controls impact image quality.

There is an increasing demand for small portable ultrasound imagingdevices that are easier to operate and that acquire good qualityultrasound images of the target anatomy. Small portable devicestypically have smaller screens, and thus less room to display the manyuser interface controls traditionally appearing on an ultrasound userinterface. On some existing ultrasound systems that provide ultrasoundimages on a touchscreen display, on-screen controls mimic the physicalcontrols of a traditional ultrasound imaging system. These types ofcontrols may obscure viewing of the ultrasound images being acquired.

There is thus a need for improved ultrasound systems and methods thatoptimize multiple imaging parameters using a single user interfacecontrol. The embodiments discussed herein may address and/or ameliorateat least some of the aforementioned drawbacks identified above. Theforegoing examples of the related art and limitations related theretoare intended to be illustrative and not exclusive. Other limitations ofthe related art will become apparent to those of skill in the art upon areading of the specification and a study of the drawings herein.

BRIEF DESCRIPTION OF THE DRAWINGS

Non-limiting examples of various embodiments of the present disclosurewill next be described in relation to the drawings, in which:

FIG. 1 shows an example user interface that may be provided on a displayof a traditional touchscreen ultrasound system;

FIG. 2 shows an example user interface of an ultrasound system thatreceives input via a single control, in accordance with at least oneembodiment of the present invention;

FIGS. 3A-3D are a sequence of user interface interactions for receivinginput to optimize image quality in the traditional touchscreenultrasound system of FIG. 1;

FIG. 4 is a flowchart diagram for steps of a method for optimizingmultiple imaging parameters using a single user control in accordancewith at least one embodiment of the present invention;

FIG. 5 is an example user interface showing image optimizationsresulting from activation of a single user interface control, inaccordance with at least one embodiment of the present invention;

FIG. 6 is an example preset tree of a traditional ultrasound imagingsystem;

FIG. 7 is an example list of presets in an ultrasound imaging system, inaccordance with at least one embodiment of the present invention; and

FIG. 8 shows a functional block diagram of an ultrasound system, inaccordance with at least one embodiment of the present invention.

DETAILED DESCRIPTION

In a first broad aspect of the present disclosure, there is provided anultrasound imaging system, including a touchscreen display; and aprocessor configured to execute instructions that cause the processor toprovide a user interface on the touchscreen display, the user interfaceincluding an ultrasound image feed and a single control for modifyingimaging depth of the ultrasound image feed. Upon receipt of input viathe single control to modify the imaging depth of the ultrasound imagefeed, the processor causes the ultrasound imaging system to: adjustfrequency of ultrasound signals being used to acquire the ultrasoundimage feed; adjust a beamformer parameter of the ultrasound signalsbeing used to acquire the ultrasound image feed; receive first imagedata of the ultrasound image feed based on the adjusted frequency andthe adjusted beamformer parameter; based on the first image data, adjustTime Gain Compensation (TGC) of the ultrasound image feed; and receivesecond image data of the ultrasound image feed based on the adjustedfrequency, beamformer parameter and TGC; so that display of the secondimage data on the touchscreen display is optimized without receipt ofadditional user input.

In some embodiments, the input for the single control is receivable viaa touch gesture on the touchscreen display. In some embodiments, thetouch gesture includes a drag gesture.

In some embodiments, the user interface is substantially free ofgraphical controls for modifying non-depth imaging parameters of theultrasound image feed. In some embodiments, these graphical controlsinclude a graphical control for modifying any one of: frequency, focusposition, number of focal zones, and TGC.

In some embodiments, the beamformer parameter is selected from the groupconsisting of: focus position, number of focal zones, receive filterfrequency, and receive sampling frequency.

In some embodiments, the TGC of the ultrasound image feed iscontinuously adjusted after receiving the second image data, so thatdisplay of subsequent image data from the ultrasound image feed isoptimized without receipt of additional user input.

In some embodiments, adjusting the TGC of the ultrasound image feedincludes determining TGC offsets across multiple imaging depths of thefirst image data. In some embodiments, the TGC offsets are for achievinga predetermined target image intensity across the multiple imagingdepths.

In another broad aspect of the present disclosure, there is provided amethod of controlling viewing of an ultrasound image feed, the methodincluding: providing a user interface on a touchscreen display, the userinterface including an ultrasound image feed and a single control formodifying imaging depth of the ultrasound image feed; receiving inputvia the single control to modify the imaging depth of the ultrasoundimage feed; upon receipt of the input, adjusting frequency of ultrasoundsignals being used to acquire the ultrasound image feed, adjusting abeamformer parameter of the ultrasound signals being used to acquire theultrasound image feed, receiving first image data of the ultrasoundimage feed based on the adjusted frequency and the adjusted beamformerparameter, based on the first image data, adjusting Time GainCompensation (TGC) of the ultrasound image feed, and receiving secondimage data of the ultrasound image feed based on the adjusted frequency,beamformer parameter and TGC; so that display of the second image dataon the touchscreen display is optimized without receipt of additionaluser input.

In some embodiments, the input for the single control is received via atouch gesture on the touchscreen display. In some embodiments, the touchgesture includes a drag gesture.

In some embodiments, the user interface is substantially free ofgraphical controls for modifying non-depth imaging parameters of theultrasound image feed. In some embodiments, the graphical controlsinclude a graphical control for modifying any one of: frequency, focusposition, number of focal zones, and TGC.

In some embodiments, the beamformer parameter is selected from the groupconsisting of: focus position, number of focal zones, receive filterfrequency, and receive sampling frequency.

In some embodiments, TGC of the ultrasound image feed is continuouslyadjusted after receiving the second image data, so that display ofsubsequent image data from the ultrasound image feed is optimizedwithout receipt of additional user input.

In some embodiments, adjusting the TGC of the ultrasound image feedincludes determining TGC offsets across multiple imaging depths of thefirst image data. In some embodiments, the TGC offsets are for achievinga predetermined target image intensity across the multiple imagingdepths.

In another broad aspect of the present disclosure, there is provided acomputer readable medium storing instructions for execution by aprocessor of a display unit for an ultrasound imaging system, thedisplay unit having a touchscreen display, wherein when the instructionsare executed by the processor, the display unit is configured to:provide a user interface on the touchscreen display, the user interfaceincluding an ultrasound image feed and a single control for modifyingimaging depth of the ultrasound image feed; and receive input via thesingle control to modify the imaging depth of the ultrasound image feed.Upon receipt of the input, the processor causes the ultrasound imagingsystem to: adjust frequency of ultrasound signals being used to acquirethe ultrasound image feed; adjust a beamformer parameter of theultrasound signals being used to acquire the ultrasound image feed;receive first image data of the ultrasound image feed based on theadjusted frequency and the adjusted beamformer parameter; based on thefirst image data, adjust Time Gain Compensation (TGC) of the ultrasoundimage feed; and receive second image data of the ultrasound image feedbased on the adjusted frequency, beamformer parameter and TGC; so thatdisplay of the second image data on the touchscreen display is optimizedwithout receipt of additional user input.

In some embodiments, the user interface is substantially free ofgraphical controls for modifying non-depth imaging parameters of theultrasound image feed.

For simplicity and clarity of illustration, where consideredappropriate, reference numerals may be repeated among the figures toindicate corresponding or analogous elements or steps. Variousultrasound images are shown in the drawings are not drawn to scale, andare provided for illustrative purposes in conjunction with thedescription. In addition, numerous specific details are set forth inorder to provide a thorough understanding of the exemplary embodimentsdescribed herein. However, it will be understood by those of ordinaryskill in the art that the embodiments described herein may be practicedwithout these specific details. In other instances, certain steps,signals, protocols, software, hardware, networking infrastructure,circuits, structures, techniques, well-known methods, procedures andcomponents have not been described or shown in detail in order not toobscure the embodiments generally described herein.

Furthermore, this description is not to be considered as limiting thescope of the embodiments described herein in any way. It should beunderstood that the detailed description, while indicating specificembodiments, are given by way of illustration only, since variouschanges and modifications within the scope of the disclosure will becomeapparent to those skilled in the art from this detailed description.Accordingly, the specification and drawings are to be regarded in anillustrative, rather than a restrictive, sense.

Referring to FIG. 1, shown there generally as 100 is an example userinterface that may be provided on a display of a traditional touchscreenultrasound system. The user interface may display an ultrasound imagefeed 102 in which a given anatomical structure 108 is viewable. The userinterface may have elements that show the imaging depth such as a scale112 and depth indicator 116. The user interface may also have a focusposition indicator 114.

As noted, traditional ultrasound system 100 may provide virtual controlsthat mimic the operation of various physical controls available onconventional ultrasound systems. Some virtual controls that allow foroptimizing of image quality are shown in FIG. 1. These virtual controlsmay include controls for modifying the imaging depth 110 (e.g., withvirtual arrow buttons for increasing and decreasing imaging depth), thefocus position of the ultrasound signals 130 (with virtual arrow buttonsfor raising or lowering the focus position), frequency of the ultrasoundsignals 120, and Time Gain Compensation (TGC) 150. There may also be abutton for performing Automatic Image Optimization (AIO) 140, which maybe selected to perform some automated image optimization with respect tothe gain and overall contrast of the displayed image.

As will be understood by persons skilled in the art, the frequencycontrols 120 are shown in a typical manner where the user is presentedwith the option to select from 3 different frequencies of the range ofpossible frequencies available on a transducer: resolution (‘RES’)providing the highest frequency and lowest penetration, penetration(‘PEN’) providing the lowest frequency and highest penetration, andgeneral (‘GEN’) providing mid-range frequencies that balance resolutionwith penetration. Similarly, the TGC controls 150 are provided in atypical manner as a set of sliders that adjust gain in specific areas ofthe image (near-, mid-, and far-field) to compensate for the effects ofultrasound signal attenuation.

Referring to FIG. 2, shown there generally as 200 is an example userinterface of an ultrasound system that receives input via a singlecontrol, in accordance with at least one embodiment of the presentinvention. As shown, the single control 110′ modifies the imaging depthof the ultrasound image feed 102. As the ‘up’ and ‘down’ buttons areused, the imaging depth may increase or decrease correspondingly and thedepth indicator 116 can be updated accordingly. Whereas traditionalultrasound systems require users to adjust a number of controls tooptimize images being displayed, the use of a single control in theultrasound system of the present embodiments may enhance user efficiencyand ease-of-use. Also, the user interface in the present embodiments canbe substantially free of graphical controls for modifying non-depthimaging parameters of the ultrasound image feed 102. This may providemore screen space to display the ultrasound image feed 102 andanatomical structures 108. As discussed below in relation to FIG. 4, thepresent embodiments can automatically adjust a number of imagingparameters based solely on the inputted imaging depth, to optimize thedisplayed image without additional user input.

Referring to FIGS. 3A-3D, shown there generally as 300-303 are asequence of user interface interactions for receiving input to optimizeimage quality in the traditional user interface of FIG. 1. FIGS. 3A-3Dshow an example sequence of user interface control inputs that may berequired to allow a user to view an anatomical feature that is deeperinto the tissue than the view that is provided in FIG. 1.

Referring again to FIG. 1, it can be seen from the shape of theultrasound image feed 102 that the ultrasound images are generated froma curvilinear transducer typically used for imaging into the abdomen. Asnoted above, the transducer may emit ultrasound signals at a range offrequencies. As shown, the anatomical feature 108 is roughly between‘1-4 cm’ deep into the tissue (as is shown by the depth indicator 116).Since this is relatively shallow for a curvilinear transducer, thefrequency control 120 may be set to the ‘RES’ setting so that imaging isperformed at the higher frequencies the transducer is capable of. Also,the focus position may be set to be roughly near the middle of theanatomical structure 108 at roughly ‘2 cm’ deep, so that the anatomicalstructure 108 can be viewed clearly.

To image deeper into the tissue, a user may traditionally use theon-screen controls in a manner shown in FIGS. 3A-3D. Shown generally as300 in FIG. 3A, the user may first use the imaging depth controls 110(e.g., button ‘312’ shown in bolded outline) to increase the imagingdepth of the ultrasound image feed 102. This may result in the imagingdepth of the ultrasound image feed 102 being increased to ‘10 cm’ (asshown on the depth indicator 116 in FIG. 3A). In this view, theanatomical feature 108 remains viewable. However, because the frequencyof the ultrasound signals being used to generate the ultrasound imagefeed 102 remains at the high-frequency ‘RES’ setting, the ultrasoundsignals may not penetrate deep enough into the tissue to allow foranatomical structures in the far field 310 to be discerned. This mayresult in the far field 310 of the ultrasound image feed 102 appearingdark (as shown with cross-hatch shading in FIG. 3A).

To increase the penetration of the ultrasound signals being used toimage at the increased imaging depth of ‘10 cm’, a user may next use thefrequency controls 120 to decrease the frequency of the ultrasoundsignals being used to acquire ultrasound image feed 102. For example,shown generally as 301 in FIG. 3B, the user may activate the frequencycontrols 120 to select to the lower-frequency ‘PEN’ mode (shown ashighlighted with bolded box 320 in FIG. 3B). This may result in thelower-frequency signals penetrating deeper into the tissue being imagedso as to be able to generate corresponding echoes that allow deepertissues to be discerned and imaged in the ultrasound image feed 102. Inthe example illustration of FIG. 3B, it can be seen that although thefar field 310 of the ultrasound image feed 102 may remain dark (stillshown with cross-hatch shading), the use of the ‘PEN’ mode frequenciesmay allow for deeper penetration so as to allow another anatomicalstructure 308 to be viewable. As will be understood by persons skilledin the art, the use of the lower frequency ‘PEN’ mode 320 allows fordeeper penetration at the expense of resolution. Accordingly, FIG. 3Balso show the border lines of the anatomical structures 108, 308becoming less well-defined. This is shown in FIG. 3B by the anatomicalfeatures 108, 308 being illustrated with jagged lines.

A next step that a user may take to improve the quality of the imagebeing viewed can be to change the focus position of the ultrasoundsignals being used to acquire images for the ultrasound image feed 102.In FIGS. 3A and 3B, the focus position did not change from what wasshown in FIG. 1 and remained at ‘2 cm’ (as shown via the focus positionindicator 114 a, 114 b). Referring now to FIG. 3C, shown there generallyas 302 is how traditional on-screen controls on a touchscreen may nextbe used to lower the focus position deeper into the tissue. As shown,the focus position controls 130 may be used and a ‘down’ arrow button330 (shown in bolded outline) may be selected to lower the focusposition to around ‘5 cm’ (as indicated by the new position of the focusposition indicator 314). The lowering of the focus position maygenerally result in the portion of the image where the focus is moved tobecoming brighter, so that the near field 360 of the image appearsrelatively darker (shown in FIG. 3C with cross-hatch shading). Also, thefar field 310 of the image may remain dark (also shown in FIG. 3C withcross-hatch shading).

Since the ultrasound image being shown in FIG. 3C is still not showingthe various anatomical features 108, 308 with sufficient brightnessthroughout the various imaging depths, a next step that the user maytake is to perform an AIO operation. Referring to FIG. 3D, shown theregenerally as 303 is a further user interface subsequent to the one shownin FIG. 3C. As shown, the AIO button 140 (shown in bolded outline inFIG. 3D) may be selected to optimize the gain and overall contrast ofthe displayed image. For example, this may involve automaticallyadjusting the TGC controls 350.

As will be understood by persons skilled in the art, TGC is provided byincreasing gain with depth in a stepwise manner according to a number ofdepth zones (e.g., near-, mid-, and far-fields). A default gain increaseis applied in each depth zone (based on the expected average loss in thezone) in an attempt to provide a uniform background level throughout thefield of view. Traditionally, the slider TGC controls then allow formanual adjustment of the default gain applied in each zone (either toreduce the gain applied or further enhance it).

Referring back to FIG. 1 where the imaging depth was ‘3.5 cm’, it can beseen that the TGC controls (shown as a set of sliders arranged in acolumn for adjusting near-, mid-, and far-field gain from top to bottom)were set in a manner where no adjustments were made to the gain slidersin the mid-field and the far-field (the sliders remained in theirrespective middle positions). However, the gain was slightly reduced inthe near-field (the slider is positioned slightly to the left of themiddle position) where the image may have been too bright.

Referring now to FIGS. 3A-3C, it can be seen that as various otherimaging parameter controls 110, 120, 130 were being adjusted, the TGCcontrols 150 remained unmodified. Referring simultaneously to FIG. 3D,the activation of the AIO button 140 may result in the TGC controlsbeing modified so that they appear in the manner shown in control 350.Particularly, the slider for the far-field has been increased from thedefault gain setting to brighten the far field 310 of the ultrasoundimage feed 102 (which appeared dark in FIG. 3C). Similarly, the sliderfor the near-field has been increased from the previousless-than-default setting to brighten the near field 360 of theultrasound image feed (which also appeared dark in FIG. 3C). As a resultof the automatic gain adjustments made by activation of the AIO button140 (as reflected in the TGC controls 350), the image in the ultrasoundimage feed 102 may show substantially uniform brightness throughout theimaging depths, so as to allow both the anatomical features 108, 308within the field of view to be displayed more clearly.

As can be seen by FIGS. 3A-3D, traditional systems typically requireinput via a number of different virtual controls to modify various ofthe imaging parameters before an optimized image can be displayed. Asdiscussed below, the present embodiments may allow input to be receivedvia a single user interface control without the complexity and timetypically required for user interface control input by traditionalsystems.

Referring to FIG. 4, shown there generally as 400 is a flowchart diagramfor steps of a method for optimizing multiple imaging parameters using asingle user control in accordance with at least one embodiment of thepresent invention. The method may also be considered a method forcontrolling viewing of an ultrasound image feed. The method may beperformed by a computing device having a touchscreen display configuredto communicate with an ultrasound transducer and display ultrasoundimages, such the display unit discussed in relation to FIG. 8. Indiscussing the method of FIG. 4, reference will simultaneously be madeto the example user interfaces shown in FIGS. 2 and 5.

At 405, the touchscreen display may provide a user interface with asingle control for modifying imaging depth of an ultrasound image feed.For example, ultrasound signal data may be generated from scanningtissue and the resultant live image feed being displayed on atouchscreen interface such as is shown in FIG. 2. As noted above, FIG. 2shows an example embodiment of a user interface of an ultrasound systemthat receives input via a single control. Referring simultaneously toFIG. 2, it can be seen the user interface of the ultrasound system has asingle control 110′ (the ‘+’ and ‘−’ buttons) for adjusting imagingdepth of the ultrasound image feed 102. Also shown in FIG. 2 (and FIG.5) is a focus indicator similar to 114 in FIG. 1. However, in variousembodiments, the focus indicator may be omitted to further enhancesimplicity of the user interface.

At 410, the method may include receiving input via the single control tomodify the imaging depth of the ultrasound image feed 102. In relationto the example shown in FIG. 2, the input may involve pressing of the‘+’ button in the imaging depth controls 110′ to increase the imagingdepth of the ultrasound image feed 102. As illustrated in FIG. 2, thedepth control input is provided via ‘+’ and ‘−’ buttons 110; however, invarious embodiments, the single control may be provided in any form.

For example, in some embodiments, the depth control input may beprovided in the form of a touch gesture (e.g., a drag gesture) as isdescribed in U.S. patent application Ser. No. 15/336,775 entitled“Systems and Methods for Controlling Visualization of Ultrasound ImageData”, the entire contents of which are incorporated herein byreference. Other gestures for inputting the depth change may also bepossible. In some embodiments, a camera on the display may be configuredto recognize gestures to increase or decrease depth. Additionally oralternatively, the gyroscope and/or accelerometer may be configured tosense motion on the display device and translate such motion gesture(e.g., a twist or tilt gesture) as an input to increase or decreaseimaging depth.

Upon receipt of input via the single control, acts 415 to 435 may beperformed prior to an optimized ultrasound image feed 102 having theincreased imaging depth is displayed.

Act 415 involves adjusting frequency of ultrasound signals being used toacquire the ultrasound image feed 102. As noted, higher frequencyultrasound signals provide higher resolution, but they are unable topenetrate as deep into tissue as lower frequency ultrasound signals. Assuch, modification of the ultrasound signal frequency may be performedin accordance with the ultrasound frequencies available on thetransducer and the imaging depth that is desired. For example, if theinput via the single control is to increase imaging depth, the frequencyof the ultrasound signals may be decreased to enhance penetration.Conversely, if the input via the single control is to decrease imagingdepth, less penetration may be required so the frequency of theultrasound signals may be increased so as to take advantage of increasedresolution provided by the higher frequency signals.

Act 420 involves adjusting a beamformer parameter of the ultrasoundsignals being used to acquire the ultrasound image feed 102. As will beunderstood by persons skilled in the art, transducers are typically madeup of an array of small elements that can be selectively excited togenerate ultrasound waves. Since the waves generated by these individualsmall elements will constructively interfere with each other whenpulsed, the timing and sequence in which the elements are selected to bepulsed may allow a beam to be formed during a transmit function.Corresponding sum and delay operations can then be taken into accountduring reception to form one or more lines in a generated ultrasoundimage.

One example of a beamformer parameter that can be adjusted at act 420 isthe focus position of the ultrasound signals being emitted. The transmitultrasound signals may be focused at particular imaging depth to obtainbetter images of tissues at that depth. For example, as noted above withrespect to FIG. 3C, doing so may traditionally cause the resultantultrasound image to display a brighter band where the focus position is.

Another example of a beamformer parameter that may additionally oralternatively be adjusted is the number of focal zones. Although notdiscussed above with regards to the sequence of user interfaceinteractions in FIGS. 3A-3D, another manual user interface interactionthat may be inputted in traditional systems is to increase the number offocal zones. As will be understood by persons skilled in the art,modifying the focus position of the imaging depth may improve imaging oftissues at the depth where the signals are focused. However, the tissuesat the depths where the ultrasound signals are not focused may lackclarity. To improve imaging across multiple depths, it is possible toadd one or more focal zones when acquiring a single image frame, so thatmultiple ultrasound signals focused at different respective depths areprojected and received. The image data from the multiple ultrasoundsignals are then combined into a single image frame that has improvedimaging clarity at the different depths.

The trade-off for adding focal zones is a reduced frame rate due toadditional transmit/receive events being required to generate a singleimage frame. However, the reduced frame rate may be acceptable in someinstances because the perceived impact of the reduced frame rate maydiffer depending on the imaging depth. For example, at deep imagingdepths (e.g., 8-30 cm), ultrasound signals are required to traverse agreater distance so multiple transmit/receive events may take a longertime to complete than if the transmit/receive events were implemented atshallower imaging depths (e.g., 1-6 cm, where the ultrasound signalsneed to only traverse a shorter distance and a frame with multiple focalzones can be generated more quickly). This allows the reduced frame rateresulting from adding focal zones to not be as severe when imaging inshallower depths, versus when imaging at deeper depths.

At act 420, in some embodiments, the number of focal zones may beincreased or decreased as the imaging depth changes in view of the abovefactors. In one embodiment (e.g., when imaging using a linear transducerthat operates at higher frequencies for imaging more superficialstructures), the number of focal zones may be increased as imaging depthis increased to enhance image clarity across multiple imaging depths.The increased time to acquire image frames may be acceptable in thisinstance because imaging is being performed at relatively shallow depths(e.g., less than 6 cm), such that the lower frame rate may not be sosevere for a user.

In another embodiment (e.g., when imaging using a curvilinear transducerthat operates at lower frequencies for imaging tissues deeper into thebody), the number of focal zones may be decreased as imaging depth isincreased so as to preserve a desired frame rate. In this instance, atthe shallower imaging depths for the curvilinear transducer, it may bedesirable to use multiple focal zones to obtain increased imagingclarity because a desired frame rate can still be maintained (e.g.,since the distance traversed by the multiple ultrasound signals is notso great). However, as imaging depth is increased, maintaining or addingfocal zones may have too significant a negative impact on frame rate. Asa result, the number of focal zones is decreased. Conversely, in thisexample, the number of focal zones may be increased if imaging depth isdecreased, so as to enhance imaging quality while still maintaining adesired frame rate.

Further example beamformer parameters that may additionally oralternatively be modified at act 420 include the receive filterfrequency and/or receive sampling frequency. As noted above with respectto act 415, the frequency of ultrasound signals used to acquireultrasound images may be adjusted depending on the inputted imagingdepth. In various embodiments, as the transmission frequency is beingadjusted based on the imaging depth change, the receive frequency mayalso be adjusted to match the transmission frequency. Additionally oralternatively, the receive sampling frequency can be optimized to matchthe number of ultrasound samples taken to the vertical pixels in thedisplay area. For example, this may remove potential aliasing and/orenhance optimization of image processing algorithms post beamforming.

Having adjusted frequency and a beamformer parameter at acts 415 and420, the TGC settings can be adjusted to improve the image beingdisplayed. For example, as shown above in relation to FIG. 3C, usingpre-existing TGC settings to acquire an image after modifying frequencyand focus position may result in an image that has does not have uniformbrightness throughout various imaging depths. Acts 425-435 may thusrelate to an automatic TGC adjustment operation.

At 425, the method involves receiving first image data of the ultrasoundimage feed based on the adjusted frequency and the adjusted beamformerparameter. This first image data may form the baseline image intensityfor various regions of the ultrasound image feed 102 (e.g., the baselineimage intensity curve) that the adjusted TGC offsets are to be applied.

At 430, based on the first image data, the TGC settings of theultrasound image feed 102 may be adjusted. The TGC adjustments may beperformed with respect to a target image intensity for various regionsof the ultrasound image feed 102 (e.g., the target image intensitycurve), so that the TGC offsets are applied in a manner so as tosubstantially achieve the target image intensity curve. In variousembodiments, the target intensity curve may be a stored setting for theultrasound machine set by the ultrasound machine's manufacturer. In someembodiments, the target intensity across multiple imaging depths may beconfigurable user settings that can be pre-set prior to imaging, so thatthe TGC adjustments made at act 430 are configured to achieve suchinputted target intensities. Such user setting may be considered ageneral setting that impacts the desired overall brightness of theultrasound image feed 102.

Act 435 involves receiving second image data of the ultrasound imagefeed based on the adjusted frequency, beamformer parameter and TGC. Oncethe TGC offsets for the adjusted frequency and beamformer parameter aredetermined, additional image data may be received. The TGC offsets canthen be applied to this additional data so as to provide the secondimage data that substantially matches the target intensity curve.

Acts 425-435 above have been described at a high-level, and variousadditional acts may be performed when performing an automatic TGCoperation. In some embodiments, the adjustment of TGC may be performedaccording to the methods described in U.S. patent application Ser. No.14/939,993 entitled “Systems and Methods for Automatic Time GainCompensation in a Handheld Ultrasound Imaging System”, the entirecontents of which are incorporated herein by reference.

Act 440 involves displaying the second image data on the touchscreendisplay without receipt of additional user input. By performing acts 415to 435 in an automated fashion solely upon input received via the singledepth control 110′ (as shown in FIG. 2), the second image data thatreflects these adjustments may appear optimized when displayed.

Referring to FIG. 5, shown there generally as 500 is an example userinterface with image optimizations resulting from activation of a singleuser interface control, in accordance with at least one embodiment ofthe present invention. FIG. 5 displays an example user interface thatmay be shown after activation of the depth control 110′ shown in FIG. 2.In the illustrated example, the ‘+’ button 510 (shown with boldedoutline) may be selected (e.g., repeatedly pressed or held) to increasethe imaging depth to ‘10 cm’. With the activation of a single controlrelated to imaging depth, it can be seen that the ultrasound image feed102 can be configured to show both anatomical features 108, 308 withinthe field of view in a manner that provides substantially similarbrightness across various imaging depths. Similar to the anatomicalfeatures 108, 308 shown in FIGS. 3B-3D, the anatomical features 108, 308shown in FIG. 5 is illustrated with jagged lines to indicate theautomatically-adjusted lower frequency ultrasound signals used toacquire such images provide increased penetration but lower resolution.

Accordingly, the ultrasound image feed 102 shown in FIG. 5 may providean image quality that is substantially similar to what is shown in FIG.3D—but without the requirement of multiple user inputs that is requiredin traditional systems (as was discussed above with respect to FIGS.3A-3D). The present embodiments may simplify usability of an ultrasoundimaging system. For example, the ability to obtain optimized imagesbased solely on imaging depth may allow ultrasound operators to focus onthe tissue they are attempting to image, without being overly concernedabout the physics behind acquiring ultrasound images. This userinterface may be more intuitive to novice ultrasound users.

In the embodiment shown in FIG. 5, the user interface 500 is alsosubstantially free of a graphical control for modifying any one of:frequency, beamformer parameters (e.g., focus position, number of focalzones), and TGC. This is because modification of these imagingparameters can be automated based solely on the single imaging depthcontrol, as described above. The reduced number of virtual controls mayallow for the ultrasound image feed 102 to occupy more of the screen.This may enhance viewing of the ultrasound image feed 102, especially onsmaller screen sizes such as on smartphones which may have screens assmall as 3.5″ in diagonal length.

In some embodiments, the TGC of the ultrasound image feed 102 may becontinuously adjusted after receiving the second image data at act 440of FIG. 4. This may allow display of subsequent image data from theultrasound image feed to continually be optimized without receipt ofadditional user input as aspects of the tissue being imaged changes, forexample.

Referring to FIG. 6, shown there generally as 600 is an example presettree for a curvilinear transducer to be used with a traditionalultrasound imaging system. In traditional ultrasound systems (e.g., suchas those discussed above with respect to FIGS. 1, and 3A-3D), a largenumber of presets are made available to select the type of imaging to beperformed. For example, as shown, eighteen (18) presets are madeavailable. The different presets provide pre-configured sets of imagingparameters that are suited for particular types of medical examinations.Due in part to the large number of controls (and thus imagingparameters) that can be adjusted, these presets attempt to provide userswith simpler starting points to begin imaging, instead of requiringusers to manually adjust the many controls to a point where the bestimage quality can be obtained for the desired examination type.

Referring to FIG. 7, shown there generally as 700 is an example list ofpresets for a curvilinear transducer in an ultrasound imaging system ofat least one embodiment of the present invention. As shown, the presetlist has only five (5) available presets. In contrast with the presettree shown in FIG. 6, the ultrasound imaging system of the presentembodiments can provide a simpler preset list that may be lessintimidating to users. Since a number of the imaging parameters can beautomatically adjusted based on the input provided via the singleimaging depth control, the presets can be configured on a more genericbasis that leaves the fine-tuning of parameters traditionally associatedwith specific presets to be adjusted automatically during imaging.

This may allow the presets of the present embodiments to simply bedirected to configuration of settings that are not imaging parameters.For example, the presets may be for making available certain softwarefunctionality (e.g., measurement packages) for a given type of medicalexamination. As shown in FIG. 7, the ‘OB/GYN’ (obstetrics andgynecology) preset may be configured in a manner substantially similarto the ‘Abdomen’ preset, except that in the ‘OB/GYN’ preset, certain‘OB/GYN’ measurement packages typically used during such examinationsmay be made available. In another example, a preset may be forconfiguring the transducer to behave in a different mode. As shown inFIG. 7, a ‘Cardiac’ preset may be provided to configure a curvilinearprobe to operate in a phased manner using a limited number of availabletransducer elements (as is described in U.S. patent application Ser. No.15/207,203 entitled “Methods and Apparatus for Performing Multiple Modesof Ultrasound Imaging using a Single Ultrasound Transducer”, the entirecontents of which are incorporated herein by reference). Since thepresets need not provide default settings for imaging parameters, thepreset list can be shorter and thus more accessible and easier tonavigate.

Referring to FIG. 8, shown there generally as 800 is a functional blockdiagram of an ultrasound system, in accordance with at least oneembodiment of the present invention. For example, the ultrasound imagingsystem 800 may be configured to perform the method of FIG. 4, providethe user interfaces shown in FIGS. 2 and 5, and the preset list shown inFIG. 7.

Ultrasound imaging system 800 may include an ultrasound acquisition unit804 configured to transmit ultrasound energy to a target object, receiveultrasound energy reflected from the target object, and generateultrasound image data based on the reflected ultrasound energy. Theultrasound acquisition unit 804 may include a transducer 826 whichconverts electric current into ultrasound energy and vice versa.Transducer 826 may transmit ultrasound energy to the target object whichechoes off the tissue. The echoes may be detected by a sensor intransducer 826 and relayed through a bus 832 to a processor 836.Processor 836 may interpret and process the echoes to generate imagedata of the scanned tissue. In some embodiments, the ultrasoundacquisition unit 804 (or various components thereof) may be provided asa handheld ultrasound probe that is in communication with othercomponents of the ultrasound imaging system 800. For example, thehandheld probe may include the transducer 826 of ultrasound acquisitionunit 804. Ultrasound acquisition unit 804 may also include storagedevice 828 (coupled to and accessible by bus 832) for storing softwareor firmware instructions, configuration settings (e.g., sequencetables), and/or ultrasound image data.

Although not illustrated, as will be apparent to one of skill in theart, the ultrasound imaging system 800 may include other components foracquiring, processing and/or displaying ultrasound image data. Theseinclude, but are not limited to: a scan generator, transmit beamformer,pulse generator, amplifier, analogue to digital converter (ADC), receivebeamformer, signal processor, data compressor, wireless transceiverand/or image processor. Each of these may be components of ultrasoundacquisition unit 804 and/or electronic display unit 802 (describedbelow).

Ultrasound imaging system 800 may include an electronic display unit 802which is in communication with ultrasound acquisition unit 804 viacommunication interfaces 822/834. In various embodiments, communicationinterfaces 822/834 may allow for wired or wireless connectivity (e.g.,via Wi-Fi™ and/or Bluetooth™) between the electronic display unit 802and the ultrasound acquisition unit 804. Electronic display unit 802 maywork in conjunction with ultrasound acquisition unit 804 to control theoperation of ultrasound acquisition unit 804 and display the imagesacquired by the ultrasound acquisition unit 804. An ultrasound operatormay interact with the user interface provided by display unit 802 tosend control commands to the ultrasound acquisition unit 804 to adjustsingle control discussed herein. The electronic display unit 802 may bea portable device, which may include a mobile device (e.g. smartphone),tablet, laptop, or other suitable device incorporating a display and aprocessor and capable of accepting input from a user and processing andrelaying the input to control the operation of the ultrasoundacquisition unit 804 as described herein.

Each of ultrasound acquisition unit 804 and display unit 802 may haveone or more input components 824, 806 and/or one or more outputcomponents 830, 812. In the FIG. 8 embodiment, ultrasound acquisitionunit 804 may include an input component 824 which is configured toaccept input from the user (e.g., to turn on the ultrasound acquisitionunit 804 or control the connection of the ultrasound acquisition unit804 to the electronic display unit 802). For example, in someembodiments, ultrasound acquisition unit 804 may also include an outputcomponent 830, such as a LED indicator light which can output the statusof the ultrasound acquisition unit 804.

In the FIG. 8 embodiment, display unit 802 may include an inputcomponent 806 configured to accept input from the user. Certain inputreceived at input component 806 may be relayed to ultrasound acquisitionunit 804 to control the operation of ultrasound acquisition unit 804.Display unit 802 may also include an output component 812, such as adisplay screen, which displays images based on image data acquired byultrasound acquisition unit 804. In particular embodiments, display unit802's input component 806 may include a touch interface layered on topof the display screen of the output component 812. Electronic displayunit 802 may also include memory 808, Random Access Memory (RAM) 814,Read Only Memory (ROM) 810, and persistent storage device 816, which mayall be connected to bus 818 to allow for communication therebetween andwith processor 820. Ultrasound acquisition unit 804 may contain memory(e.g., storage device 828) that may be accessible by processor 836. Anynumber of these memory elements may store software or firmware that maybe accessed and executed by processor 820 and/or processor 836 to, inpart or in whole, perform the acts of the methods described herein(e.g., so that the processor 820 is configured to provide the userinterfaces of FIGS. 2 and 5 discussed herein on display unit 802).

In some embodiments, all of the input controls and display screennecessary for the operation of the ultrasound imaging system 800 may beprovided by input and output components 806, 812 of the display unit802. In such cases input and output components 824, 830 of ultrasoundacquisition unit 804 may be optional and/or omitted. In certainembodiments, the ultrasound acquisition unit 804 may be a handheld probe(i.e. including transducer 826) which is in communication with thedisplay unit 802 over the communications interfaces 822/834 tofacilitate operation of the ultrasound acquisition unit 804 andprocessing and display of ultrasound images.

In various embodiments, at least a portion of the processing of theimage data corresponding to the reflected ultrasound energy detected bythe handheld probe's transducer 826 may be performed by one or more ofprocessors internal to the ultrasound acquisition unit 804 (such as bythe processor 836) and/or by processors external to the ultrasoundacquisition unit 804 (such as the processor 820 of electronic displayunit 802). By having some of the image data processing tasks typicallyperformed by a processor 836 of ultrasound acquisition unit 804 beperformed instead by a processor 820 of the display unit 802, lessphysical processing hardware may need to be provided on the ultrasoundacquisition unit 804. This may facilitate a lightweight, portable designand construction for the ultrasound acquisition unit 804 (e.g., when itis a handheld probe). In particular embodiments the handheld probe mayhave a mass that is less than approximately 1 kg (2 lbs).

In some embodiments, the output component 830 of ultrasound acquisitionunit 804 may include a display screen, which can be configured todisplay or otherwise output the images acquired by ultrasoundacquisition unit 804 (in addition to or alternative to displaying suchimages on the display unit 802).

As noted, the ultrasound imaging system 800 of FIG. 8 may be configuredto perform the method of FIG. 4, so as to receive the touch input anddisplay the user interfaces in FIGS. 2 and 5. The discussion below willbe made with simultaneous reference to FIGS. 2 and 5, and the componentsof FIG. 8, to illustrate how such components may be involved inperforming various acts of the method of FIG. 4. Steps of method 400 inFIG. 4 may be implemented as software or firmware contained in a programmemory 808, 814, 810 or storage device 816 accessible to a processor 820of display unit 802 and/or a storage device 828 accessible to processor836 of ultrasound acquisition unit 804. Processor 820/836 mayindependently or collectively implement various acts of method 400 ofFIG. 4 by executing software instructions provided by the software.

For example, when doing so, the initial imaging parameters shown in thelive ultrasound image feed may be defined by the current or initialimaging parameters of ultrasound acquisition unit 804 and/or electronicdisplay unit 802. The current or initial imaging parameters may havebeen pre-loaded to the electronic display unit 802 (e.g. frommanufacturer's settings) based on the initial imaging depth.

Ultrasound image data may be obtained, for example, by ultrasoundacquisition unit 804 employing a high frequency, high voltage pulse toexcite transducer 826 to emit ultrasound waves and receiving thereflected ultrasound waves. In particular embodiments, the ultrasoundacquisition unit 804 may be a probe which acquires ultrasound image databy generating pulses of a specified amplitude in accordance with anultrasound sequence specified in a sequence table. The probe may performultrasound beam generation using transmit beamforming, detects andreceives the ultrasound echo and performs receive beamforming, andprocesses the data based on the sequence specified in the sequencetable. The probe may transmit the processed ultrasound image data to adisplay unit 802 which has a processor 820 that further processes thedata for display (e.g. scan conversion) and then displays the ultrasoundimage on the output component (e.g., screen) 812.

Scan conversion may then be performed on the data to transform the imagedata in a manner that allows it to be displayed in a form that is moresuitable for human visual consumption. For example, this may involveconverting the image data from the data space (e.g. polar coordinateform) to the display space (e.g. Cartesian coordinate form). Theacquired ultrasound images may be displayed on the output component 812of display unit 802 (act 405 of FIG. 4). Scan conversion is one of theactions that renders the image data suitable for display. However, aswill be apparent to those of skill in the art, other technological stepsmay also need to be performed, such as, for example, amplificationand/or digitization of the data. After the scan conversion, anultrasound image may be displayed by the electronic display unit 802.

If an ultrasound operator wishes to modify the imaging depth parameter,they may input a touchscreen command to direct the ultrasound imagingsystem 100 via the single control provided on the touchscreen of theelectronic display unit 802 (act 410 of FIG. 4). For example, the inputcomponent 806 of display unit 802 may include a touch interface thatdetects the user input and interprets the command based on the userinput being received. The touchscreen interface may receive the inputand provide it to processor 820 which executes software instructions toanalyse the input and determine the command associated with the input.

Upon input via the single imaging depth control, the display unit 102may transmit the command to modify imaging depth to the ultrasoundacquisition unit 804 via communication interfaces 822, 834. In turn, theultrasound acquisition unit 804 may adjust various imaging parameterssuch as frequency and beamformer parameters used by the transducer 826to acquire ultrasound image data (acts 415-420 of FIG. 4). Then, newimage data may be acquired and a TGC operation performed on the newimage data at either the display unit 802 and/or the ultrasoundacquisition unit 804 (acts 425-435 of FIG. 4). These operations may helpoptimize visualization of the acquired image data. The optimized imagedata may then be displayed on the output component 812 (e.g., atouchscreen display) of the electronic display unit 802 (act 440 of FIG.4).

While a number of exemplary aspects and embodiments have been discussedabove, those of skill in the art will recognize that may be certainmodifications, permutations, additions and sub-combinations thereof.While the above description contains many details of exampleembodiments, these should not be construed as essential limitations onthe scope of any embodiment. Many other ramifications and variations arepossible within the teachings of the various embodiments.

INTERPRETATION OF TERMS

Unless the context clearly requires otherwise, throughout thedescription and the claims:

-   -   “comprise”, “comprising”, and the like are to be construed in an        inclusive sense, as opposed to an exclusive or exhaustive sense;        that is to say, in the sense of “including, but not limited to”;    -   “connected”, “coupled”, or any variant thereof, means any        connection or coupling, either direct or indirect, between two        or more elements; the coupling or connection between the        elements can be physical, logical, or a combination thereof;    -   “herein”, “above”, “below”, and words of similar import, when        used to describe this specification, shall refer to this        specification as a whole, and not to any particular portions of        this specification;    -   “or”, in reference to a list of two or more items, covers all of        the following interpretations of the word: any of the items in        the list, all of the items in the list, and any combination of        the items in the list;    -   the singular forms “a”, “an”, and “the” also include the meaning        of any appropriate plural forms.

Unless the context clearly requires otherwise, throughout thedescription and the claims:

Words that indicate directions such as “vertical”, “transverse”,“horizontal”, “upward”, “downward”, “forward”, “backward”, “inward”,“outward”, “vertical”, “transverse”, “left”, “right”, “front”, “back”,“top”, “bottom”, “below”, “above”, “under”, and the like, used in thisdescription and any accompanying claims (where present), depend on thespecific orientation of the apparatus described and illustrated. Thesubject matter described herein may assume various alternativeorientations. Accordingly, these directional terms are not strictlydefined and should not be interpreted narrowly.

Embodiments of the invention may be implemented using specificallydesigned hardware, configurable hardware, programmable data processorsconfigured by the provision of software (which may optionally comprise“firmware”) capable of executing on the data processors, special purposecomputers or data processors that are specifically programmed,configured, or constructed to perform one or more steps in a method asexplained in detail herein and/or combinations of two or more of these.Examples of specifically designed hardware are: logic circuits,application-specific integrated circuits (“ASICs”), large scaleintegrated circuits (“LSIs”), very large scale integrated circuits(“VLSIs”), and the like. Examples of configurable hardware are: one ormore programmable logic devices such as programmable array logic(“PALs”), programmable logic arrays (“PLAs”), and field programmablegate arrays (“FPGAs”). Examples of programmable data processors are:microprocessors, digital signal processors (“DSPs”), embeddedprocessors, graphics processors, math co-processors, general purposecomputers, server computers, cloud computers, mainframe computers,computer workstations, and the like. For example, one or more dataprocessors in a control circuit for a device may implement methods asdescribed herein by executing software instructions in a program memoryaccessible to the processors.

For example, while processes or blocks are presented in a given orderherein, alternative examples may perform routines having steps, oremploy systems having blocks, in a different order, and some processesor blocks may be deleted, moved, added, subdivided, combined, and/ormodified to provide alternative or subcombinations. Each of theseprocesses or blocks may be implemented in a variety of different ways.Also, while processes or blocks are at times shown as being performed inseries, these processes or blocks may instead be performed in parallel,or may be performed at different times.

The invention may also be provided in the form of a program product. Theprogram product may comprise any non-transitory medium which carries aset of computer-readable instructions which, when executed by a dataprocessor (e.g., in a controller and/or ultrasound processor in anultrasound machine), cause the data processor to execute a method of theinvention. Program products according to the invention may be in any ofa wide variety of forms. The program product may comprise, for example,non-transitory media such as magnetic data storage media includingfloppy diskettes, hard disk drives, optical data storage media includingCD ROMs, DVDs, electronic data storage media including ROMs, flash RAM,EPROMs, hardwired or preprogrammed chips (e.g., EEPROM semiconductorchips), nanotechnology memory, or the like. The computer-readablesignals on the program product may optionally be compressed orencrypted.

Where a component (e.g. a software module, processor, assembly, device,circuit, etc.) is referred to above, unless otherwise indicated,reference to that component (including a reference to a “means”) shouldbe interpreted as including as equivalents of that component anycomponent which performs the function of the described component (i.e.,that is functionally equivalent), including components which are notstructurally equivalent to the disclosed structure which performs thefunction in the illustrated exemplary embodiments of the invention.

Specific examples of systems, methods and apparatus have been describedherein for purposes of illustration. These are only examples. Thetechnology provided herein can be applied to systems other than theexample systems described above. Many alterations, modifications,additions, omissions, and permutations are possible within the practiceof this invention. This invention includes variations on describedembodiments that would be apparent to the skilled addressee, includingvariations obtained by: replacing features, elements and/or acts withequivalent features, elements and/or acts; mixing and matching offeatures, elements and/or acts from different embodiments; combiningfeatures, elements and/or acts from embodiments as described herein withfeatures, elements and/or acts of other technology; and/or omittingcombining features, elements and/or acts from described embodiments.

It is therefore intended that the following appended claims and claimshereafter introduced are interpreted to include all such modifications,permutations, additions, omissions, and sub-combinations as mayreasonably be inferred. The scope of the claims should not be limited bythe preferred embodiments set forth in the examples, but should be giventhe broadest interpretation consistent with the description as a whole.

What is claimed is:
 1. An ultrasound imaging system, comprising: atouchscreen display; and a processor configured to execute instructionsthat cause the processor to provide a user interface on the touchscreendisplay, the user interface comprising an ultrasound image feed and asingle control for modifying imaging depth of the ultrasound image feed;wherein upon receipt of input via the single control to modify theimaging depth of the ultrasound image feed, the processor causes theultrasound imaging system to: adjust frequency of ultrasound signalsbeing used to acquire the ultrasound image feed, adjust a beamformerparameter of the ultrasound signals being used to acquire the ultrasoundimage feed, receive first image data of the ultrasound image feed basedon the adjusted frequency and the adjusted beamformer parameter, basedon the first image data, adjust Time Gain Compensation (TGC) of theultrasound image feed, and receive second image data of the ultrasoundimage feed based on the adjusted frequency, beamformer parameter andTGC; so that display of the second image data on the touchscreen displayis optimized without receipt of additional user input.
 2. The ultrasoundimaging system of claim 1, wherein the input for the single control isreceivable via a touch gesture on the touchscreen display.
 3. Theultrasound imaging system of claim 2, wherein the touch gesturecomprises a drag gesture.
 4. The ultrasound imaging system of claim 1,wherein the user interface is substantially free of graphical controlsfor modifying non-depth imaging parameters of the ultrasound image feed.5. The ultrasound imaging system of claim 4, wherein the graphicalcontrols comprise a graphical control for modifying any one of:frequency, focus position, number of focal zones, and TGC.
 6. Theultrasound imaging system of claim 1, wherein the beamformer parameteris selected from the group consisting of: focus position, number offocal zones, receive filter frequency, and receive sampling frequency.7. The ultrasound imaging system of claim 1, wherein TGC of theultrasound image feed is continuously adjusted after receiving thesecond image data, so that display of subsequent image data from theultrasound image feed is optimized without receipt of additional userinput.
 8. The ultrasound imaging system of claim 1, wherein adjustingthe TGC of the ultrasound image feed comprises determining TGC offsetsacross multiple imaging depths of the first image data.
 9. Theultrasound imaging system of claim 8, wherein the TGC offsets are forachieving a predetermined target image intensity across the multipleimaging depths.
 10. A method of controlling viewing of an ultrasoundimage feed, the method comprising: providing a user interface on atouchscreen display, the user interface comprising an ultrasound imagefeed and a single control for modifying imaging depth of the ultrasoundimage feed; receiving input via the single control to modify the imagingdepth of the ultrasound image feed; upon receipt of the input, adjustingfrequency of ultrasound signals being used to acquire the ultrasoundimage feed, adjusting a beamformer parameter of the ultrasound signalsbeing used to acquire the ultrasound image feed, receiving first imagedata of the ultrasound image feed based on the adjusted frequency andthe adjusted beamformer parameter, based on the first image data,adjusting Time Gain Compensation (TGC) of the ultrasound image feed, andreceiving second image data of the ultrasound image feed based on theadjusted frequency, beamformer parameter and TGC; so that display of thesecond image data on the touchscreen display is optimized withoutreceipt of additional user input.
 11. The method of claim 10, whereinthe input for the single control is received via a touch gesture on thetouchscreen display.
 12. The method of claim 11, wherein the touchgesture comprises a drag gesture.
 13. The method of claim 10, whereinthe user interface is substantially free of graphical controls formodifying non-depth imaging parameters of the ultrasound image feed. 14.The method of claim 13, wherein the graphical controls comprise agraphical control for modifying any one of: frequency, focus position,number of focal zones, and TGC.
 15. The method of claim 10, wherein thebeamformer parameter is selected from the group consisting of: focusposition, number of focal zones, receive filter frequency, and receivesampling frequency.
 16. The method of claim 10, wherein TGC of theultrasound image feed is continuously adjusted after receiving thesecond image data, so that display of subsequent image data from theultrasound image feed is optimized without receipt of additional userinput.
 17. The method of claim 10, wherein adjusting the TGC of theultrasound image feed comprises determining TGC offsets across multipleimaging depths of the first image data.
 18. The method of claim 17,wherein the TGC offsets are for achieving a predetermined target imageintensity across the multiple imaging depths.
 19. A computer readablemedium storing instructions for execution by a processor of a displayunit for an ultrasound imaging system, the display unit having atouchscreen display, wherein when the instructions are executed by theprocessor, the display unit is configured to: provide a user interfaceon the touchscreen display, the user interface comprising an ultrasoundimage feed and a single control for modifying imaging depth of theultrasound image feed; and receive input via the single control tomodify the imaging depth of the ultrasound image feed; wherein uponreceipt of the input, the processor causes the ultrasound imaging systemto: adjust frequency of ultrasound signals being used to acquire theultrasound image feed, adjust a beamformer parameter of the ultrasoundsignals being used to acquire the ultrasound image feed, receive firstimage data of the ultrasound image feed based on the adjusted frequencyand the adjusted beamformer parameter, based on the first image data,adjust Time Gain Compensation (TGC) of the ultrasound image feed, andreceive second image data of the ultrasound image feed based on theadjusted frequency, beamformer parameter and TGC; so that display of thesecond image data on the touchscreen display is optimized withoutreceipt of additional user input.
 20. The computer readable medium ofclaim 19, wherein the user interface is substantially free of graphicalcontrols for modifying non-depth imaging parameters of the ultrasoundimage feed.